Vacuum surge suppressor for surgical aspiration systems

ABSTRACT

An apparatus and method to suppress vacuum surges in a surgical aspiration system is disclosed and claimed. A vacuum surge suppressor includes a first fluid path for coupling to a surgical instrument, and a filter attached to the first fluid path. A flow restrictor is coupled to the filter with the filter disposed upstream of the flow restrictor. The filter defines a filter longitudinal axis that may be oriented vertically with respect to gravity, so that a downstream direction at the filter is upwards. The vacuum surge suppressor also includes a second fluid path for coupling to a vacuum pump. The second fluid path is connected to the flow restrictor and disposed downstream of the flow restrictor. A third fluid path is coupled to the filter and is connected to the second fluid path, bypassing the flow restrictor. A valve in the third fluid path selectively obstructs or permits flow in the third fluid path.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims benefit under 35 U.S.C. §120 as acontinuation-in-part of pending U.S. patent application Ser. No.13/019,972, entitled “VACUUM SURGE SUPPRESSOR FOR SURGICAL ASPIRATIONSYSTEMS,” filed on Feb. 2, 2011, hereby incorporated by reference, whichclaims benefit under 35 U.S.C. §120 as a continuation of pending U.S.patent application Ser. No. 12/109,586, entitled “VACUUM SURGESUPPRESSOR FOR SURGICAL ASPIRATION SYSTEMS,” filed on Apr. 25, 2008,hereby incorporated by reference, and which claims priority under 35U.S.C. §119(e) to U.S. Provisional Application No. 60/934,497, entitled“VACUUM SURGE SUPRESSOR WITH ADJUSTABLE FLOW PATH,” filed on Jun. 13,2007, also hereby incorporated by reference.

FIELD OF THE INVENTION

The present invention relates generally to the field of medical devicesused in surgery, and more particularly to aspiration systems used insurgery.

BACKGROUND

Various contemporary surgical procedures require aspiration of fluidsthat may contain solid or semi-solid tissue or other debris. In manycases, the fluids may need to be aspirated from a body cavity such asthe lens capsule of the eye or a cavity in a joint such as the shoulderor the knee. It is typically desirable to maintain an ambient or asuper-ambient pressure within the body cavity during such surgicalprocedures.

For example, the lens of a human eye may develop a cataracteouscondition that affects a patient's vision. Cataracteous lenses aresometimes removed and replaced in a procedure commonly referred to asphacoemulsification. Phacoemulsification procedures are typicallyperformed with an ultrasonically driven hand piece that is used to breakthe lens within the lens capsule of the eye. The broken lens is removedthrough an aspiration line that is coupled to the hand piece andprotrudes into the lens capsule. The hand piece has a tip that isinserted through an incision in the cornea. The hand piece typicallycontains a number of ultrasonic transducers that convert electricalpower into a mechanical oscillating movement of the tip. The distal endof the tip has an opening that is in fluid communication with theaspiration line. The distal end of the tip also has a sleeve that has anopening in fluid communication with an irrigation line. The irrigationline is typically connected to a bottle that can provide irrigationfluid to the surgical site. The oscillating movement of the tip breaksthe lens into small pieces. The lens pieces and irrigation fluid aredrawn into the aspiration line through the opening of the tip.

Phacoemulsification is more likely to be successful if ambient orsuper-ambient pressure can be maintained within the lens capsule and theanterior chamber of the eye during the procedure. However, vacuum surgescan be created when the aspiration line is momentarily obstructed bysolid or semi-solid tissue. Such vacuum surges can lead to transientaspiration flow rates through the aspiration line that substantiallyexceed the flow rate through the irrigation line and thereby cause asub-ambient pressure to be momentarily applied to the surroundingtissue. The momentary sub-ambient pressure condition may cause anundesirable collapse of the anterior chamber of the eye, undesirabledamage to the posterior aspect of the lens capsule of the eye, and/orendothelium cells to be undesirably drawn away from the cornea andtowards the distal end the tip of the hand piece. On the other hand, toohigh an irrigation flow rate may undesirably move endothelium cells awayfrom the cornea, or undesirably cause endothelium cells to be aspiratedout of the eye.

Conventional phacoemulsification procedures are typically performedusing a vacuum pressure of about 250 mmHg. There is a desire to increasethe vacuum pressure to assist in aspirating larger pieces of the lens.Aspirating larger pieces would lower the amount of ultrasonic work thatmust be performed on the eye. Lowering the ultrasonic work would bedesirable because ultrasound can irritate the eye. Consequently, thereis a desire to create vacuums up to 500 mmHg to improve aspiration andreduce the amount of ultrasound delivered to the cornea. However, suchhigher pressures exacerbate the surgical risks associated with vacuumsurges.

Also for example, some orthopedic medical procedures produce particlesor other debris that must be removed from a cavity within a joint suchas in the shoulder or knee. To remove such particles the surgeon maycouple an aspiration tube to the surgical site. The aspiration tube,which pulls the debris from the body, is typically connected to acanister, which is connected to a suction tube connected to wallsuction. To ensure that the surgical site is properly distended duringsurgery, relatively large quantities of irrigation fluid are typicallyintroduced to the body to continuously irrigate the surgical site, andan infusion pump is typically required to offset the high flow createdby the hospital vacuum line. The introduction of such amounts ofirrigation fluid into the body can cause undesirable or excessiveextravagation of irrigation fluid into the surrounding tissue. Also,vacuum surges can be created when the suction line is obstructed bysolid or semi-solid tissue. Such vacuum surges can lead to transientaspiration flow rates through the hospital vacuum line thatsubstantially exceed the flow rate of irrigation fluid and thereby causea sub-ambient pressure to be momentarily applied to the surroundingtissue. The momentary sub-ambient pressure condition may cause partialcollapse of the body cavity, damage to tissue near the distal end of theaspiration tube, and/or undesired tissue or fluid to be drawn towardsthe distal end of the aspiration tube.

Surgical aspiration systems may be designed to allow the surgeon totemporarily reverse the direction of aspiration flow by depressing areflux bulb attached to the system. The surgeon may do this, forexample, if tissue is drawn towards the distal tip of the aspirationtube or hand piece that the surgeon does not desired to be drawn (e.g.tissue that the surgeon does not want to be damaged by the distal tip).The surgeon may also initiate reflux to clear or dislodge an occlusionat the distal tip of the aspiration tube or hand piece.

Contemporary flow restrictors can limit the vacuum surges within theaspiration system, but only when the vacuum created by the vacuum pumpis limited to a level that is safe in consideration of the diameter andlength of that flow restrictor. For example, considering the typicaldimensions of needles and tubings used in ophthalmology, the flow thatwould be generated by a 500 mmHg vacuum is in excess of 250 cc/min,which could undesirably completely collapse an eye. Therefore, prior artsystems that use a venturi pump must operate modest vacuum levels, e.g.below 200 mmHg unless very small needles are used. Such modest vacuumlevels significantly limit the available un-occluded flow in suchsystems. Therefore, such flow restrictors are typically not used withperistaltic pumps that will significantly increase the pressuredifference in response to an occlusion of the aspiration tip. Theabsence of pressure rise in response to occlusion in the contemporaryaspiration systems limits their ability to aspirate large tissueparticles. Also, an in-line flow restrictor may reduce the maximum flowrate in the absence of occlusion, even when the surgeon would prefer ahigher flow rate to draw certain tissue towards the distal end of thetip (rather than moving the distal end of the tip towards the tissue).Also, an in-line flow restrictor can undesirably reduce the maximumreflux flow rate.

Therefore, it would be desirable to provide a surgical aspiration systemthat maintains an ambient or super-ambient pressure within a body cavityduring a surgical procedure by limiting vacuum surges in the system. Forexample, it would be desirable to provide an aspiration system that isconfigured such that the flow rate out of the body cavity through theaspiration line does not greatly, or for a prolonged period, exceed theflow rate into the body cavity. In cataract surgery, for example,aspiration flow should be sufficient to quickly engage and aspirate lensparticles from the eye, however in the event of an occlusion the highvacuum created in the aspiration line may temporarily produce too high aflow which could collapse the eye. Therefore, it would also be desirableto provide a surgical aspiration system that functions safely withlimited or reduced flow rate of irrigation fluid through the irrigationline. It would also be desirable to provide an aspiration system thatcan safely take advantage of the use of a peristaltic pump (or anotherpump type that can significantly increase the relative vacuum responseto an occlusion). It would also be desirable to provide an aspirationsystem that would allow a high aspiration flow rate in the absence of anocclusion, and a high reflux flow rate when needed by the surgeon.

SUMMARY

An apparatus and method to suppress vacuum surges in a surgicalaspiration system is disclosed and claimed. A vacuum surge suppressorincludes a first fluid path for coupling to a surgical instrument, and afilter attached to the first fluid path. A flow restrictor is coupled tothe filter with the filter disposed upstream of the flow restrictor. Thefilter defines a filter longitudinal axis that may be orientedvertically with respect to gravity, so that a downstream direction atthe filter is upwards. The vacuum surge suppressor also includes asecond fluid path for coupling to a vacuum pump. The second fluid pathis connected to the flow restrictor and disposed downstream of the flowrestrictor. A third fluid path is coupled to the filter and is connectedto the second fluid path, bypassing the flow restrictor. A valve in thethird fluid path selectively obstructs or permits flow in the thirdfluid path.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a schematic depiction of a vacuum surge suppressor accordingto an embodiment of the present invention.

FIG. 2 is an example graph of vacuum and flow versus time according toan embodiment of the present invention.

FIG. 3 is a schematic depiction of a vacuum surge suppressor accordingto another embodiment of the present invention.

FIG. 4 is a schematic depiction of a vacuum surge suppressor accordingto another embodiment of the present invention.

DETAILED DESCRIPTION

FIG. 1 is a schematic depiction of a vacuum surge suppressor 100according to an embodiment of the present invention. Fluid and solidmaterial from an irrigated surgical site may be aspirated through inputtubing 110, also referred to as the “aspiration line.” During normaloperation, the input tubing 110 would be coupled to a surgicalinstrument such as a hand piece designed to facilitate surgery in a bodycavity (e.g. a phacoemulsification hand piece). Coupling to the surgicalinstrument can be accomplished by attachment to the surgical instrumentor to another fluid pathway that itself is coupled to the surgicalinstrument. Filter 112, which is depicted in FIG. 1 as being an in-linefilter that is disposed in filter housing 114 and coupled to inputtubing 110, retains larger particles of the aspirated material such thatonly small particles can pass through the filter 112.

In the embodiment of FIG. 1, a flow restrictor 116 is disposeddownstream of the filter housing 114. The term “downstream” as usedherein, does not imply the necessity for any flow or fluid in the systemas claimed. Rather, “downstream” is used herein only to indicate adirection to facilitate discussion of the relative position ofcomponents within the system, by referring to flow that would occurduring periods of normal operation without reflux, and serves thepurpose of facilitating such discussion even for systems that are notpresently in use and contain no fluid or flow. Likewise, “upstream”means that a component would be normally upstream if installed in anoperating system; it does not require any flow or fluid in the vacuumsurge suppressor component when it is not installed in an operablesystem or when an operable system is not operating. The filter housing114 may have various shapes but is preferably tapered at the entranceinto the flow restrictor 116 to reduce the formation of air bubbles. Theflow restrictor 116 preferably comprises an orifice defining an orificeinner diameter in the range 0.005 to 0.025 inches and an orifice lengthin the range 1 to 2 inches. For example, the orifice may be designed tohave an inner diameter of 0.010 inches and a length of 1 inch. Theorifice preferably has fixed dimensions because it is difficult for anorifice that allows adjustment to achieve the desired precision. Forexample, a restriction of 0.02 inch diameter will allow 16 times moreflow then a 0.01 inch diameter because flow is proportional with the 4thpower of diameter.

In the embodiment of FIG. 1, output tubing 118 is disposed downstream ofthe flow restrictor 116. During normal operation, the output tubing 118would be coupled to a vacuum pump designed to create a sub-ambientpressure in output tubing 118. Coupling to the vacuum pump can beaccomplished by attachment to the vacuum pump or attachment to theoutput tubing 118 or another fluid pathway that itself is coupled to theoutput tubing 118. The sub-ambient pressure pumps used in ophthalmicinstrumentation are commonly called “vacuum pumps” even though they donot create an absolute vacuum but rather create a pressure that is belowambient pressure but still greater than zero absolute pressure. “Vacuum”is used herein in the relative sense rather than in an absolute sense,so that “vacuum” refers to the magnitude of the pressure differencebetween ambient pressure and a sub-ambient pressure that corresponds tothe vacuum. Therefore, as used herein, vacuum is said to increase whenthe corresponding sub-ambient pressure falls to a lower absolutepressure value that is further from the ambient pressure, and vacuum issaid to decrease when the corresponding sub-ambient pressure rises to ahigher absolute value that is closer to ambient pressure.

In the embodiment of FIG. 1, for example, a venturi pump may be coupledto output tubing 118 to create a relatively constant vacuum therein.Alternatively, for example, a peristaltic pump may be coupled to outputtubing 118 to create a vacuum will increase if/when the flow isoccluded. A pressure sensor 120 coupled to the output tubing 118 maysense the vacuum in the output tubing 118. For example, the pressuresensor 120 may be attached to the output tubing 118 as shown in FIG. 1.The pressure sensor 120 is preferably a transducer that is capable ofsensing the path internal pressure in the output tubing 118, andproviding an electrical potential, signal, or other electricalcharacteristic (e.g. electrical impedance) that is responsive to suchpath internal pressure. The pressure sensor may be designed to senserelative pressure rather than absolute pressure, for example providingan electrical potential, signal, or other electrical characteristic thatis indicative of the vacuum in the output tubing 118.

In the embodiment of FIG. 1, bypass tubing 124 is coupled to the filterhousing 114 and to the output tubing 118, in a way that bypasses theflow restrictor 116. Bypass tubing 124 may be coupled to the filterhousing 114 by being connected to the filter housing 114, as shown inFIG. 1, or alternatively by being connected to a fluid path that isitself connected to the filter housing 114. Likewise, bypass tubing 124may be coupled to the output tubing 118 by being connected to the outputtubing 118 as shown in FIG. 1, or alternatively by being connected to afluid path that is itself connected to the output tubing 118. In eithercase, under normal operation the bypass tubing 124 carries a flow thatbypasses the flow restrictor 116. In the embodiment of FIG. 1, bypasstubing 124 need not be “rigid” tubing but is preferably flexible tubingthat does not collapse in response to sub-ambient pressure at sea level.The bypass tubing 124 may, for example, comprise so-called hard silicontubing.

Moreover, bypass tubing 124 may be and/or may include a valve 122 thatcan substantially interrupt the flow in bypass tubing 124 in response tothe path internal pressure of the output tubing 118. For example, thevalve 122 may be a discrete automated valve (e.g. a solenoid-drivenvalve) that is responsive to an output 126 of the pressure sensor 120.The output 126 of the pressure sensor 120 may be conditioned and/oramplified by other conventional circuitry. For example, if the pressuresensor 120 provides a time-varying voltage that is responsive to pathinternal pressure, such time-varying voltage may be amplified by anamplifier and/or conditioned by a logic circuit to create the output126. Optionally, the amplifier may be an inverting amplifier, forexample if it is desired that decreasing relative pressure (i.e.increasing vacuum) would correspond to increasing voltages. Also forexample, if the pressure sensor 120 provides a time-varying electricalimpedance that is responsive to path internal pressure, suchtime-varying impedance may be detected by an analog circuit and perhapsby digital sampling, and then be further conditioned by a logic circuitto create the output 126. Such a logic circuit might, for example,provide a constant voltage to valve 122 (e.g. to keep it open if it is anormally closed solenoid valve) and discontinue such (allowing the valve122 to close) only when the time-varying voltage or impedance exceeds orfalls below a certain threshold. Alternatively, the amplification and/orlogic circuitry may be included with the valve 122 so that the output126 that is shown in FIG. 1 corresponds to the raw, unconditioned outputof the pressure sensor. In either case, the action of the valve 122 isresponsive to the pressure sensed by the pressure sensor 120, by aconventional means.

FIG. 2 is an example graph 200 of vacuum 250 and total flow 230 throughoutput tubing 118, versus time (increasing to the right along time axis260), to illustrate the manner of operation of an embodiment of thepresent invention. At the far left side 210 of the graph 200, the vacuum250 is sensed by sensor 120 to be less than a preset safety threshold240 (e.g. a vacuum level less than 250 mmHG, such as 200 mmHg), so thevalve 122 is kept open and flow passes through bypass tubing 124. Theavailability of the bypass tubing 124 for flow allows the total flow 230to be at a high value. Such a high flow condition may be desirable insurgery; for example in phacoemulsification surgery it may be useful toquickly attract lens material into the surgeon's hand piece. Moreover,the availability of open bypass tubing 124 may advantageously facilitatethe creation of reflux flow by the surgeon at the surgeon's discretion,without such reflux flow being constrained by the flow restrictor 116.

However, at a later time 212 the flow 230 is occluded (for example bysolid material being aspirated into the surgical instrument that iscoupled to the input tubing 110), so that the flow 230 becomes zero andthe vacuum 250 rapidly increases (assuming that the pump that is coupledto output tubing 118 is a peristaltic pump rather than a venturi pump).At a time between time 212 and time 214, the vacuum 250 is sensed bysensor 120 to have increased above the preset safety threshold 240, sothat the valve 122 is closed, blocking flow through the bypass tubing124 so that subsequent flow must pass through the flow restriction 116.At time 214 the vacuum 250 reaches a maximum that the pump is configuredto produce (e.g. 500 mmHg or more). The flow 230 remains nearly zero atthis time, however, because the occlusion has not yet passed.

At time 216, the occlusion finally passes so that the vacuum 250 canonce again cause flow 230 to rise. Since the vacuum 250 is at a highlevel, the flow 230 would rise rapidly to a dangerously high level (thatcould have adverse surgical effects) if not for the valve 122 beingclosed so that all of the flow 230 must pass through the flow restrictor116. Instead, the flow 230 only rises to a safe level that is permittedby the flow restrictor 116, though the damping introduced by the flowrestrictor 116 may not completely suppress the flow overshoot. Betweentimes 216 and 218, the moderate flow 230 causes the vacuum 250 todiminish until it is sensed by sensor 120 to have fallen below thepresent safety threshold 240. Then (i.e. at time 218) the valve 122 isre-opened, allowing flow through the bypass tubing 124 so that the totalflow 230 rises back to its pre-occlusion high level. The higher flow 230causes the vacuum 250 to diminish further until, at time 220, it reachesits pre-occlusion low level.

Thus, in the manner shown in FIG. 2, the embodiment of FIG. 1 enablessafe transitions from a non-occluded, high-flow, low-vacuum condition,to an occluded, low-flow, high-vacuum condition, and back again. Throughthe actions of valve 122 and flow restrictor 116, surges in flow due topost-occlusion periods of high vacuum are moderated to prevent adversesurgical effects. In phacoemulsification procedures, for example, suchadverse surgical effects may include collapse of the anterior chamber ofthe eye, undesired aspiration of endothelium cells, and/or damage to theposterior aspect of the lens capsule.

The embodiment of FIG. 1 may employ a venturi pump rather than aperistaltic pump, in which case it preferably also includes vacuumcontrol switches controllable by the surgeon using a foot pedal. Oneswitch may increase the vacuum and the other decrease the vacuum withinpreset limits. Whereas the range of adjustment typically could notsafely exceed 10% in prior art devices, this range may be increasedsignificantly (e.g. 100%) using the embodiment of FIG. 1. For example,if the threshold is set to 250 mmHg, then the surgeon can operate below250 mmHg with unrestricted flow. However, if/when the surgeon feels thatmore vacuum is necessary at a certain time he/she can safely raise thevacuum above the threshold up to the highest limit of the pump (e.g. 600mmHg) in which case the flow will be restricted by flow restrictor 116of FIG. 1.

FIG. 3 is a schematic depiction of a vacuum surge suppressor 300according to another embodiment of the present invention. In theembodiment of FIG. 3, input tubing 310 is coupled to filter housing 314,which contains filter 312, and output tubing 318 is coupled to flowrestrictor 316. For example, the input tubing 310 may be coupled tofilter housing 314 by being attached to filter housing 314, and theoutput tubing 318 may be coupled to flow restrictor 316 by beingattached to flow restrictor 316. The flow restrictor 316 is coupled tofilter housing 314, for example by being attached to filter housing 314or being part of filter housing 314. Bypass tubing 324 is coupled to thefilter housing 314 and to the output tubing 318, in a way that bypassesthe flow restrictor 316.

In the embodiment of FIG. 3, the bypass tubing 324 comprises collapsibletubing (e.g. thin, collapsible silicone tubing). The collapsible bypasstubing 324 is designed (e.g. by specifying tubing wall thickness) suchthat the tubing collapses when the vacuum exceeds a preset threshold(e.g. 200 mmHg). In this manner, the collapsible bypass tubing 324 ofthe embodiment of FIG. 3 serves the combined functions of the pressuresensor 120, the valve 122, and the bypass tubing 124 in the embodimentof FIG. 1. That is, when the collapsible bypass tubing 324 of theembodiment of FIG. 3 collapses, the majority of flow must then passthrough the flow restrictor 316 and the system operates in a manner thatis similar to that described with reference to FIG. 2. Although theembodiment of FIG. 3 has reduced complexity and cost relative to theembodiment of FIG. 1, the embodiment of FIG. 1 may allow the vacuumthreshold 240 to be dynamically changed under software control. Thevacuum threshold 240 in the embodiment of FIG. 3 is determined bymaterial properties and so is not easily controlled and may beundesirably affected by environmental conditions such as temperature.

FIG. 4 is a schematic depiction of a vacuum surge suppressor 400according to another embodiment of the present invention. Fluid andsolid material from an irrigated surgical site may be aspirated throughinput tubing 410, also referred to as the “aspiration line.” Duringnormal operation, the input tubing 410 would be coupled to a surgicalinstrument such as a hand piece designed to facilitate surgery in a bodycavity (e.g. a phacoemulsification hand piece). Coupling to the surgicalinstrument can be accomplished by attachment to the surgical instrumentor to another fluid pathway that itself is coupled to the surgicalinstrument.

The embodiment of FIG. 4, includes a filter 412 that is an in-linefilter disposed in a filter housing 414 and coupled to input tubing 410.The filter 412 retains larger particles of the aspirated material suchthat only small particles can pass through the filter 412. Although thedirection of gravitational acceleration is not specified in FIGS. 1 and3 (so that the various elements shown in those figures may have anyorientation with respect to gravitational acceleration), the filterhousing 414 shown in FIG. 4 is expressly depicted to be orientedvertically with respect to gravitational acceleration g. In certainembodiments, the vertical and upward orientation of the flow through thefilter 412 and filter housing 414 increases the likelihood that thefilter will fully prime, such that it is less likely for bubbles orpackets of air to become trapped inside the filter 412 or the filterhousing 414.

In the embodiment of FIG. 4, a flow restrictor 416 is disposeddownstream of the filter housing 414. The entrance into the flowrestrictor 416 is preferably tapered to reduce the formation of airbubbles. The flow restrictor 416 preferably comprises an orificedefining an orifice inner diameter in the range 0.005 to 0.025 inchesand an orifice length in the range 1 to 2 inches. For example, theorifice may be designed to have an inner diameter of 0.010 inches and alength of 1 inch. The orifice preferably has fixed dimensions because itis difficult for an orifice that allows adjustment to achieve thedesired precision. For example, a restriction of 0.02 inch diameter willallow 16 times more flow then a 0.01 inch diameter because flow isproportional with the 4th power of diameter.

In the embodiment of FIG. 4, output tubing 418 is disposed downstream ofthe flow restrictor 416. During normal operation, the output tubing 418would be coupled to a vacuum pump designed to create a sub-ambientpressure in output tubing 418. Coupling to the vacuum pump can beaccomplished by attachment to the vacuum pump or attachment to theoutput tubing 418 or another fluid pathway that itself is coupled to theoutput tubing 418. In the embodiment of FIG. 4, for example, a venturipump may be coupled to output tubing 418 to create a relatively constantvacuum therein. Alternatively, for example, a peristaltic pump may becoupled to output tubing 418 to create a vacuum will increase if/whenthe flow is occluded.

In the embodiment of FIG. 4, bypass tubing 124 is coupled to the filterhousing 414 and to the output tubing 418, in a way that bypasses theflow restrictor 416. Bypass tubing 424 may be coupled to the filterhousing 414 by being connected to the filter housing 414, oralternatively by being connected to a fluid path that is itselfconnected to the filter housing 414, as shown in FIG. 4. Likewise,bypass tubing 424 may be coupled to the output tubing 418 by beingconnected to the output tubing 418 as shown in FIG. 4, or alternativelyby being connected to a fluid path that is itself connected to theoutput tubing 418. In either case, under normal operation the bypasstubing 424 carries a flow that bypasses the flow restrictor 416. In theembodiment of FIG. 4, bypass tubing 424 need not be “rigid” tubing butis preferably flexible tubing that does not collapse in response tosub-ambient pressure at sea level. The bypass tubing 424 may, forexample, comprise so-called hard silicon tubing.

Moreover, bypass tubing 424 may be and/or may include a valve 422 thatcan substantially interrupt the flow in bypass tubing 424 in response toa command input by the operating physician or surgeon. For example, inthe embodiment of FIG. 4, the valve 422 may be a solenoid-driven valvethat is responsive to a driving signal 426 that passes through aconventional switch or potentiometer that is manipulated by aconventional foot pedal 420, which is controlled by the operatingphysician or surgeon. It is also possible for the valve 422 to becontrolled by the foot pedal 420 via a conventional mechanical linkageto the foot pedal 420, or via a conventional hydraulic pressureconnection to a conventional hydraulic piston at the foot pedal 420.

In certain embodiments of the present invention, such manual control ofthe valve 422 (e.g. by a surgeon's manipulation of the foot pedal 420)may be preferred to automatic control of the valve 422 in response tothe output of a pressure sensor. For example, some surgeons may preferto use high vacuum for an entire surgical procedure, while others mayprefer to use low vacuum but high flow during the entire surgicalprocedure. Manual control of the valve 422 (e.g. via foot pedal 420) maysatisfy either preference, so that the same device might be used,advantageously reducing inventory.

Alternatively, in certain embodiments of the present invention, the footpedal 420 may be used by the surgeon or operating physician to changethe state of valve 422 at different phases of the same surgicalprocedure. For example, in phacoemulsification, the extraction of theeye lens may have three phases in which a different vacuum level may bedesired. In the first phase, a low vacuum and high flow may bepreferred, while in the second phase a high vacuum may be preferred, andthen in the third phase a moderate vacuum may be preferred.

In the foregoing specification, the invention is described withreference to specific exemplary embodiments, but those skilled in theart will recognize that the invention is not limited to those. It iscontemplated that various features and aspects of the invention may beused individually or jointly and possibly in a different environment orapplication. The specification and drawings are, accordingly, to beregarded as illustrative and exemplary rather than restrictive. Forexample, the word “preferably,” and the phrase “preferably but notnecessarily,” are used synonymously herein to consistently include themeaning of “not necessarily” or optionally. “Comprising,” “including,”and “having,” are intended to be open-ended terms.

1. A vacuum surge suppressor, for a surgical aspiration system thatincludes a surgical instrument and a vacuum pump, the vacuum surgesuppressor comprising: a first fluid path for coupling to the surgicalinstrument; a filter attached to the first fluid path, the filterdefining a filter longitudinal axis that is oriented vertically withrespect to gravity so that a downstream direction at the filter isupwards; a flow restrictor coupled to the filter, the flow restrictorcomprising an orifice defining a fixed orifice inner diameter in therange 0.005 to 0.025 inches and a fixed orifice length in the range 1 to2 inches, the filter being disposed upstream of the flow restrictor; asecond fluid path for coupling to the vacuum pump, the second fluid pathconnected to the flow restrictor and disposed downstream of the flowrestrictor, the second fluid path defining a path internal pressure; athird fluid path coupled to the filter and connected to the second fluidpath, bypassing the flow restrictor; and a valve in the third fluid paththat obstructs flow in the third fluid path in response to the pathinternal pressure.
 2. The vacuum surge suppressor of claim 1 wherein thefirst fluid path comprises a tube adapted to be connected to acorresponding tube of the surgical instrument.
 3. The vacuum surgesuppressor of claim 1 wherein the second fluid path comprises a tubeadapted to be connected to a corresponding tube of the vacuum pump. 4.The vacuum surge suppressor of claim 1 wherein the filter includes afilter housing, and the first fluid path is connected to the filterhousing.
 5. The vacuum surge suppressor of claim 1 wherein the filterincludes a filter housing, and the flow restrictor is connected to thefilter housing.
 6. The vacuum surge suppressor of claim 5 wherein thethird fluid path is connected to the filter housing.
 7. The vacuum surgesuppressor of claim 1 further comprising a pressure sensor capable ofsensing the path internal pressure, and wherein the valve is a discreteautomated valve that is responsive to an output of the pressure sensor.8. The vacuum surge suppressor of claim 7 wherein the third fluid pathcomprises a rigid plastic tube.
 9. The vacuum surge suppressor of claim7 wherein the discrete automated valve is a solenoid driven valve. 10.The vacuum surge suppressor of claim 1 wherein the filter is an in-linefilter.
 11. A vacuum surge suppressor, for a surgical aspiration systemthat includes a surgical instrument and a vacuum pump, the vacuum surgesuppressor comprising: a first fluid path for coupling to the surgicalinstrument; a filter attached to the first fluid path; a flow restrictorcoupled to the filter, the flow restrictor comprising an orificedefining a fixed orifice inner diameter in the range 0.005 to 0.025inches and a fixed orifice length in the range 1 to 2 inches, the filterbeing disposed upstream of the flow restrictor; a second fluid path forcoupling to the vacuum pump, the second fluid path connected to the flowrestrictor and disposed downstream of the flow restrictor; a third fluidpath coupled to the filter and connected to the second fluid path,bypassing the flow restrictor; and a valve in the third fluid path thatselectively obstructs or permits flow in the third fluid path inresponse to a human control input.
 12. The vacuum surge suppressor ofclaim 11 wherein the filter includes a filter housing that is orientedvertically with respect to gravity so that a downstream direction at thefilter is upwards, and wherein the first fluid path is connected to thefilter housing.
 13. The vacuum surge suppressor of claim 12 wherein thefilter is an in-line filter.
 14. The vacuum surge suppressor of claim 11wherein the discrete automated valve is a solenoid driven valve.
 15. Thevacuum surge suppressor of claim 11 wherein the first fluid pathcomprises a tube adapted to be connected to a corresponding tube of thesurgical instrument.
 16. The vacuum surge suppressor of claim 11 whereinthe second fluid path comprises a tube adapted to be connected to acorresponding tube of the vacuum pump.
 17. The vacuum surge suppressorof claim 11 wherein the human control input is administered by a footpedal.
 18. The vacuum surge suppressor of claim 17 wherein the footpedal is attached to a device selected from the list consisting of aswitch, a potentiometer, and a hydraulic piston.